Classifications

• • A—HUMAN NECESSITIES
  • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
  • A61K—PREPARATIONS FOR MEDICAL, DENTAL OR TOILETRY PURPOSES
  • A61K9/00—Medicinal preparations characterised by special physical form
  • A61K9/0012—Galenical forms characterised by the site of application
  • A61K9/0019—Injectable compositions; Intramuscular, intravenous, arterial, subcutaneous administration; Compositions to be administered through the skin in an invasive manner
  • A61K9/0024—Solid, semi-solid or solidifying implants, which are implanted or injected in body tissue
• • A—HUMAN NECESSITIES
  • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
  • A61K—PREPARATIONS FOR MEDICAL, DENTAL OR TOILETRY PURPOSES
  • A61K47/00—Medicinal preparations characterised by the non-active ingredients used, e.g. carriers or inert additives; Targeting or modifying agents chemically bound to the active ingredient
  • A61K47/30—Macromolecular organic or inorganic compounds, e.g. inorganic polyphosphates
  • A61K47/34—Macromolecular compounds obtained otherwise than by reactions only involving carbon-to-carbon unsaturated bonds, e.g. polyesters, polyamino acids, polysiloxanes, polyphosphazines, copolymers of polyalkylene glycol or poloxamers
• • A—HUMAN NECESSITIES
  • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
  • A61L—METHODS OR APPARATUS FOR STERILISING MATERIALS OR OBJECTS IN GENERAL; DISINFECTION, STERILISATION OR DEODORISATION OF AIR; CHEMICAL ASPECTS OF BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES; MATERIALS FOR BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES
  • A61L31/00—Materials for other surgical articles, e.g. stents, stent-grafts, shunts, surgical drapes, guide wires, materials for adhesion prevention, occluding devices, surgical gloves, tissue fixation devices
  • A61L31/04—Macromolecular materials
  • A61L31/06—Macromolecular materials obtained otherwise than by reactions only involving carbon-to-carbon unsaturated bonds
• • A—HUMAN NECESSITIES
  • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
  • A61L—METHODS OR APPARATUS FOR STERILISING MATERIALS OR OBJECTS IN GENERAL; DISINFECTION, STERILISATION OR DEODORISATION OF AIR; CHEMICAL ASPECTS OF BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES; MATERIALS FOR BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES
  • A61L31/00—Materials for other surgical articles, e.g. stents, stent-grafts, shunts, surgical drapes, guide wires, materials for adhesion prevention, occluding devices, surgical gloves, tissue fixation devices
  • A61L31/14—Materials characterised by their function or physical properties, e.g. injectable or lubricating compositions, shape-memory materials, surface modified materials
  • A61L31/145—Hydrogels or hydrocolloids
• • C—CHEMISTRY; METALLURGY
  • C08—ORGANIC MACROMOLECULAR COMPOUNDS; THEIR PREPARATION OR CHEMICAL WORKING-UP; COMPOSITIONS BASED THEREON
  • C08G—MACROMOLECULAR COMPOUNDS OBTAINED OTHERWISE THAN BY REACTIONS ONLY INVOLVING UNSATURATED CARBON-TO-CARBON BONDS
  • C08G63/00—Macromolecular compounds obtained by reactions forming a carboxylic ester link in the main chain of the macromolecule
  • C08G63/66—Polyesters containing oxygen in the form of ether groups
  • C08G63/664—Polyesters containing oxygen in the form of ether groups derived from hydroxy carboxylic acids

Definitions

• the resulting hydrogel displays higher elasticity compliance and tensils strength while being absorbable.
• the SIBS systems are, in some respects, anlogous to thermoreversible gels (Shalaby, in Water-Soluble Polymers, (Shalaby, S.W., et al., Eds.), Vol. 467, Chapt. 33, ACS Symp. Ser., Amer. Chem. Soc., Washington, DC, 1991a) in displaying a hydration-dehydration equilibrium governing the system transformation, i.e., the gel/liquid equilibrium is driven by the water content of the SIBS.
• the polyoxyalkylene blocks undergo intermolecuiar segmental mixing with the neighboring hydrophobic blocks to produce a viscous liquid.
• competition between the water as an extrinsic solvent and the polyester block for the polyoxyalkylene (POA) block forces the hydration of the POA, and aggregation or association of the polyester blocks to establish pseudo-crosslinks which maintain a 3-dimensional integrity.
• the POA block will preferentially migrate to the exterior of the gel and interface with the adjoining tissues to establish an adhesive joint, which prevents gel migration from target site and sustains its intended efficacy.
• hydrogels most often cited in the literature are those made of water-soluble polymers, such as polyvinyl pyrrolidone, which have been crosslinked with naturally derived biodegradable components such as those based on albumin (Park, et. al., 1993, cited elsewhere herein; and W. Shalaby, et. al., 1992, cited elsewhere herein).
• Totally synthetic hydrogels which have been studied for controlled drug release and membranes for the treatment of post-surgical adhesion are based on covalent networks formed by the addition polymerisation of acrylic-terminated, water-soluble chains of polyether dl-polylactide block copolymers (Jarrett, et. al., 1995, cited elsewhere herein; and Pathak, et al., 1993, cited elsewhere herein).
• U.S. Patent No., 5,366,733, to Brizzolars et al. discloses an oral composition for the oral administration of a therapeutic agent to a periodontal pocket comprising at least one therapeutic agent dispersed in a matrix including a biocompatible and/or biodegradable polymer.
• the composition is administered as a plurality of dry discrete microparticles, said microparticles are prepared by a phase separation process.
• An oral composition is also described wherein the polymer comprises a block copolymer of polyglycolide, trimethylene carbonate and polyethylene oxide.
• Apparatus and methods are also provided for dispensing the dry microparticles to the periodontal pocket, whereby they become tacky and adhere to the involved tissue so as to induce long-term therapeutic effects.
• a further object of the present invention is to provide such a copolymer which is capable of being extruded or injected into living tissue, or onto the surface thereof, for providing a protective barrier for treating conditions, such as, post-surgical adhesion.
• Hydrogel or “Hydrogel Mass” as used herein, refers to materials which have a high tendency for water absorption and/or retention, and maintain mechanical integrity through physical crosslinks which are reversible in nature.
• hydrophobic biock X comprises a polyester formed by grafting a glycolide, lactide, ⁇ -caprolactone, p-dioxanone, trimethyIene carbonate or combinations thereof, onto the hydroxylic or amino-end groups of a hydrophilic polymer precursor i.e., Y.
• Hydrophilic block Y preferably comprises a polyoxyethylene, poly(oxyethylene-b-oxypropylene), polypeptide, polyalkylene oxamate, a polysaccharide, or derivatives thereof, or a liquid, high molecular weight polyether glycol interlinked with oxalate or succinate functionalities in linear or branched form.
• Component A with or without a non-steroidal anti-inflammatory drug (NSAID) or active polypeptide, can be used as a protective barrier, a blocking agent of vascular defects caused by needle puncturing, a sealant of damaged surfaces for preventing post-surgical adhesion or as a carrier of immunostimulants or viable cells.
• Component A, mixed with an antimicrobial agent-drug, can be injected or applied topically with a suitable known applicator for the treatment of bone, cartilage, nail, skin, and vaginal infections.
• the absorbable plasticizer such as Component C
• the absorbable plasticizer is capable of modulating the viscosity and/or gel-formation rate of Component A, with or without Component B, thereby broadening its applicability.
• Highly viscous forms of Component A can be easily plasticized with a low molecular weight (inherent viscosity of 0.03 - 0.15) polyester copolymer Component C, that is made of the same chemical entities as Component A, (but different hydrophilic weight fraction) to produce easily injectable liquid systems.
• a formulation for treating periodontal disease comprises 20/80 Components B/A, containing 1-3 % of an active drug such as chlorhexidine or tetracycline.
• the copolymer formulations of the present invention can include a variety of optional components.
• Such components include, but are not limited to, surfactants, viscosity controlling agents, medicinal agents, cell growth modulators, dyes, complexing agents, antioxidants, other polymers such as carboxymethly cellulose, gums such as guar gum, waxes/oils such as castor oil, glycerol, dibutyl phthalate and di(2-ethylhexyl) phthalate as well as many others.
• optional components comprise from about 0.1 % to about 20 %, preferably from about 0.5 % to about 5 % of the total copolymer formulation.
• Another feature of the novel copolymers of the invention is that when administered to a biological site the copolymers do not experience discernible reduction in organic mass, as is the case of prior art compositions which coagulate in-situ by leaching out a major water-soluble component. Leaching out major water-soluble components can be associated with shrinkage and separation from the surrounding tissue and, in some instances, uncontrolled formation of microporous mass. Because the copolymers of the invention are comprised of copolymeric chains, the copolymers can be easily tailored to modulate its viscosity without the intervention of a new chemical species, such as, an organic solvent.
• a suitable flask was thoroughly cleaned, flame-dried, and charged dry with polyethylene glycol (MW - 400; 5g, 0.0125 mole), dl-lactide (12 g, 0.083 mole), glycolide (6.4 g, 0.056 mole), stannous octoate catalyst (0.4 M in toluene; 34.7 ⁇ L, 0.014 mmole), and a magnetic stirrer under nitrogen condition.
• the reactor was placed in an oil bath and heated to 170°C under a positive nitrogen pressure for 16 hours.
• the flask was removed and stored open in a vacuum oven.
• the reactants were heated to 155°C for 1 hour under slight vacuum before increasing the temperature to 160°C for 2 hours under increased vacuum.
• l-Lactide (14.4 g, 0.1 mole), glycolide (7.7 g, 0.066 mole) were added under dry conditions to the reactor.
• the flask was heated to 150°C under a positive nitrogen pressure for 15 hours.
• the temperature was lowered to 130°C and vacuum was applied.
• the material bubbled violently, indicating the presence of monomer.
• a strong vacuum was applied as the material cooled to room temperature.
• the final product was washed with 2-propanol at 40°C for about 20 minutes to remove the excess monomer before drying under vacuum at room temperature.
• PEG 400 was interlinked with dimethyl oxalate (as described in Example 5) prior to the addition of dl-lactide and glycolide.
• Interlinked PEG (85 g), dl-lactide (9.0 g, 0.0625 mole), glycolide (4.83 g, 0.0417 mole), and stannous octoate catalyst (0.2 M in toluene; 105 ⁇ L, 0.05 mmole) were added to a dry glass reactor and heated to 150°C for 1 hours. The temperature was increased to 160°C for 4 more hours before removing the reactants from heat and applying a vacuum of less than 0.1 mm Hg as the material cooled to room temperature. The polymer was isolated and stored under vacuum.

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• Health & Medical Sciences (AREA)
• Chemical & Material Sciences (AREA)
• Life Sciences & Earth Sciences (AREA)
• Epidemiology (AREA)
• Veterinary Medicine (AREA)
• Public Health (AREA)
• General Health & Medical Sciences (AREA)
• Animal Behavior & Ethology (AREA)
• Medicinal Chemistry (AREA)
• Pharmacology & Pharmacy (AREA)
• Chemical Kinetics & Catalysis (AREA)
• Heart & Thoracic Surgery (AREA)
• Surgery (AREA)
• Vascular Medicine (AREA)
• Proteomics, Peptides & Aminoacids (AREA)
• Polymers & Plastics (AREA)
• Dermatology (AREA)
• Neurosurgery (AREA)
• Biomedical Technology (AREA)
• Engineering & Computer Science (AREA)
• Dispersion Chemistry (AREA)
• Inorganic Chemistry (AREA)
• Organic Chemistry (AREA)
• Medicinal Preparation (AREA)
• Polyesters Or Polycarbonates (AREA)
• Materials For Medical Uses (AREA)
• Macromonomer-Based Addition Polymer (AREA)
• Compositions Of Macromolecular Compounds (AREA)

Applications Claiming Priority (2)

Publications (3)

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Cited By (21)

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• 1995
  • 1995-04-13 US US08/421,222 patent/US5612052A/en not_active Expired - Lifetime
• 1996
  • 1996-04-04 AU AU50561/96A patent/AU685357B2/en not_active Ceased
  • 1996-04-12 EP EP96105777A patent/EP0737703B1/de not_active Expired - Lifetime
  • 1996-04-12 CA CA002174072A patent/CA2174072C/en not_active Expired - Fee Related
  • 1996-04-12 DE DE0737703T patent/DE737703T1/de active Pending
  • 1996-04-12 JP JP08091611A patent/JP3107514B2/ja not_active Expired - Fee Related
  • 1996-04-12 AT AT96105777T patent/ATE243720T1/de not_active IP Right Cessation
  • 1996-04-12 DE DE69628783T patent/DE69628783T2/de not_active Expired - Lifetime
  • 1996-10-31 US US08/740,646 patent/US5714159A/en not_active Expired - Lifetime

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